Method and apparatus for monitoring laser surgery

ABSTRACT

A method and system for laser surgery produces controlled laser pulses and simultaneously verifies that a correct sequence of pulses are being delivered to the patient. A photo detector receives a predetermined portion of the energy of the treatment pulses as they exit the system. A separate monitoring computer compares an output signal from the photo detector with reference information for the treatment sequence. The system is exemplified in an implementation in an ophthalmic laser surgery system.

RELATED APPLICATIONS

This application is a divisional of U.S. application Ser. No.09/816,175, filed Mar. 26, 2001, which is a continuation-in-part of U.S.application Ser. No. 09/359,371, filed Jul. 23, 1999, now U.S. Pat. No.6,322,555, the contents of which applications are hereby incorporated byreference.

FIELD OF THE INVENTION

This invention relates to laser surgery apparatus and methods adaptedfor use, for example, in the monitoring of laser systems used inophthalmic laser surgery.

BACKGROUND OF THE INVENTION

Laser systems have been used in ophthalmic surgery for modifying thecornea of the patient. Systems such as shown in U.S. Pat. No. 4,729,372to L'Esperance contemplate the controlled ablation of the cornea of thepatient with a pulsed excimer laser. Operations performed with thesystem include corneal transplants and keratotomies.

The application of laser light to the cornea may be controlled by spotscanning of the cornea or by the use of masks. As shown in U.S. Pat. No.5,108,388 to Trokel, the masks may, for example, employ slits or holes.Repeated scanning or pulsing through properly selected masks areemployed to reshape or reprofile the curvature of the cornea to treatmyopic or hyperopic conditions. The system can also be used, forexample, to remove corneal sections for corneal replacements ortransplants.

Three types of laser vision correction surgery techniques are known inthe art: broad beam, slit scanning and spot scanning. Broad beam systemsuse a relatively large beam (e.g. 6.0 to 8.0 mm) pulsed at a relativelylow pulse rate (e.g. 10 to 50 Hz). The spot delivered to the cornea maybe, for example, from ½ mm to 8 mm in diameter depending on the irisopening of the system set to various positions in accordance with atreatment sequence for the patient. Spot scanning systems also called“flying spot” scanners typically employ reciprocating or rotatingoptical devices to make a series of overlapping laser shots, that forexample, spiral out from the center of the cornea. Spot scanning systemsuse a relatively small spot (e.g. 1 to 2 mm in diameter). A typicaltreatment using a spot scanning system may require several thousandshots at 50 to 200 Hz. In a slit scanning laser, the laser beam isfocused through a slit in a rotational device. The slit may be graduallyenlarged to increase the ablated area on the cornea. Various scanningsystems are described, for example, in U.S. Pat. No. 6,136,012 to Chayetet al., which is hereby incorporated by reference.

A system used by applicant for performing ophthalmic laser surgery isshown in FIG. 1. The system includes an Excimer laser 10 such as aCOMPex 201 Excimer laser. An optical rail 12 contains optical elementsfor controlling the laser pulses and delivers spatially modulated pulsesto a shuttling device 14, which acts as a selectively positionableturning mirror, for directing the laser pulses to a selected one of thetwo surgical stations, 16 and 18. The system allows surgery to beperformed on one patient while a second patient is readied, and improvesthe utilization efficiency of the operating room, laser and opticalrail.

FIGS. 2(a) and (b) are vertical and horizontal cross-sectional views andray traces of an optical path which may be used in the system of FIG. 1to deliver pulses from the laser 10′ to the cornea of the patient at 20.A light beam from the laser is shaped and focused by a series of lenses22, 24 and 26. A beam homogenizer 28 is located next in the optical pathas shown. A spatial modulator 30 provides beam dimensions andorientations in accordance with predetermined treatment parametersappropriate for the surgery required by the patient. The spatialmodulator may include a conventional iris and variable, slit mask(s) aswell as controls for changing the axis of orientation of the mask(s).These systems are motor driven on command from a treatment computercontaining a treatment algorithm into which the treatment parametershave been programmed.

The shuttling turning mirror 32 selectively directs the laser beam toone or the other surgical stations along one of the system arms 34 or 36shown in FIG. 1. An imaging lens 38 is located in each arm. Pulses fromthe imaging lens are reflected by end turning mirror 40 toward thetarget area 42 on the patient's cornea.

It is important that pulses delivered to the cornea have the appropriateenergy to ensure that the reprofiling, cutting or ablation produced isconsistent with the prescribed treatment for the patient. Systems of thetype shown in FIG. 2 have employed photo detectors selectivelypositionable in the main optical path of the system at the end turningmirror for the purpose of calibrating or adjusting the energy deliveredby the system during a preliminary calibration phase. See U.S. Pat. No.5,772,656 to Kloptek.

Other control systems have been proposed such as disclosed in U.S. Pat.No. 4,941,093 to Marshall et al., which includes a measurement device tomeasure the cornea surface profile and a feedback control system tocontrol the laser operation in accordance with the measured and desiredprofiles. U.S. Pat. No. 5,423,801 to Marshall et al. discloses furthercontrol of the laser by a measurement signal from a beam-shaping meansand/or cornea while it is exposed to irradiation by the laser. U.S. Pat.No. 4,973,330 to Azema et al. discloses a photo detector associated witha semi-transparent mirror, which is intended to furnish a treatmentcomputer with information relative to the energy of the pulses exitingthe laser before the laser beam reaches the controlling device. A lasercalibration device is shown in U.S. Pat. No. 5,464,960 to Hall et al.which employs a phantom cornea with superimposed thin films ofalternating colors. U.S. Pat. No. 5,984,916 to Lai discloses a surgicallaser system with a feedback system for controlling the treatment laserbeam.

OBJECTS AND SUMMARY OF THE INVENTION

It is an object of the present invention to provide a more efficient andreliable technique for monitoring laser surgery, including broad beam,slit scanning and spot scanning systems.

It is another object of the present invention to monitor the energy ofactual laser pulses used in the ophthalmic laser surgery as they exitthe optical rail.

It is another object of the present invention to monitor a sequence oflaser pulses of varying beam dimensions and locations used in ophthalmiclaser surgery.

It is another object of the present invention to provide a parallel,fail-safe system for detecting discrepancies between a programmedtreatment and the laser pulses actually administered to the cornea ofthe patient.

These and other objects and features will be apparent from the followingdescription of the present invention contained herein.

The present invention relates to methods for laser surgery andparticularly for the modification of the cornea of a patient with alaser system in accordance with treatment parameters appropriate for thepatient and for continuously verifying that a predetermined sequence oflaser pulses of correct energy are being delivered to the cornea of thepatient. In practicing the method, pulses of laser light are generatedand controlled. The controlled pulses are simultaneously directed to thecornea of the patient and to a photo detector. Advantageously, thesystem uses a beam splitter for this purpose. The beam splitter is thelast optical element in the optical path leading to the cornea of thepatient. An output signal of the photo detector is converted into avalue representative of the light energy delivered to the cornea of thepatient. Alternatively, the photo detector may be a two-dimensionalarray of photo sensing cells capable of producing signals indicative ofthe spacial energy distribution of the treatment pulses. Such an arraymay, for example, be a CCD or CMOS device.

Light energy values may be compared to a reference values derived fromsystem calibration information and from the treatment parameters for thepatient. An indication of the performance of the laser system isprovided in response to this comparison. When a two-dimensional detectorarray is used, a histogram may be produced, displayed and stored showingthe amount of energy delivered to incremental areas of the cornea overselected time intervals.

In preferred embodiments of the invention, the pulses of laser light areproduced by a laser triggered by a triggering signal from a treatmentcomputer. The pulses of laser light may be spatially modulated orscanned responsive to signals from the treatment computer. The treatmentcomputer is programmed with the treatment parameters appropriate for thepatient. In this embodiment, the reference values are produced by amonitoring computer separately programmed with the treatment parametersappropriate for the patient. The double entry of treatment parametershelps expose data entry errors in the treatment computer, since such anerror will create a discrepancy between the light energy value and thereference value. The comparison may be initiated by the monitoringcomputer responsive to the laser triggering signal. When the lightenergy value of a predetermined number of pulses deviates apredetermined amount from the corresponding reference values, the systemmay produce an alarm signal or shut down the system.

In another preferred embodiment of the present invention, thesimultaneous directing of the spatially modulated pulses is performed bybeam-splitting the pulses to direct a portion of electromagnetic energyfrom the pulse to a photo detector. The directed portion ofelectromagnetic energy of the laser pulse may be directed through anoptical baffle to block scatter caused, for example, by fluids splashedon the beam splitter. The directed portion of the pulse may then beconverted to fluorescent light which is detected by the photo detector.One or more neutral density filters may be employed to filter thefluorescent light so that the photo detector and associated amplifierare operated in a generally linear response mode across a range ofexpected incident radiation energies.

The present invention also includes an apparatus for producing apredetermined treatment sequence of laser pulses of predetermined energyand for monitoring the energy of the pulses as the pulses are beingdelivered to the patient. Such an apparatus may include an excimer,pulsed laser, and a beam homogenizer and a spatial modulator in theoptical path of the laser. First electronic circuitry controls the laserand spatial modulator in accordance with entered data indicative of thepredetermined treatment sequence of pulses for the patient. Secondelectronic circuitry produces reference values indicative of the energyof laser pulses which should be produced by the laser, the referencevalue being calculated in accordance with separately entered dataindicative of the predetermined treatment sequence of pulses for thepatient. Advantageously, the first and second electronic circuitry areseparate, programmable digital computing devices.

A photo detector produces a monitoring signal related in value to theenergy of laser pulses delivered to the patient. Further electroniccircuitry compares the monitoring signal with the correspondingreference value calculated by the second electronic means.

As noted above, the delivered laser pulses may be monitored using a beamsplitter which is the last optical device in the system optical pathleading from the laser to the cornea of the patient. Advantageously, asecond beam splitter and a photo detector may be placed at the beginningof the optical rail to monitor laser output directly. This monitoringmay be required because the output of the laser may vary from pulse topulse or drift over the course of a single patient treatment.Advantageously, this additional detector is capable of detecting anenergy change of 2% or less from pulse to pulse. Detected changesgreater than a selected threshold level may be used to produce a warningsignal or to shut down the system.

The foregoing is intended as a convenient summary of this disclosure.However, the scope of the invention intended to be covered is indicatedby the patent claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a plan view of a two surgical station laser eye surgerysystem;

FIGS. 2(a) and (b) are, respectively, vertical and horizontalcross-sectional views of the optical path employed in the system of FIG.1 for delivering laser pulses to the cornea of the patient;

FIG. 3 is a horizontal cross-sectional view of a laser energy monitor inaccordance with a preferred embodiment of the present invention;

FIG. 3(a) is a horizontal cross-sectional view of a laser energy monitorwith an optical baffle in accordance with a preferred embodiment of thepresent invention;

FIG. 4 is a schematic block diagram illustrating process and apparatusaspects of the disclosed system for producing and monitoring laserpulses delivered to the cornea of a patient in accordance with thepresent invention;

FIG. 5 is a schematic block diagram illustrating the use of an areaarray detector and histogram in a scanning spot laser surgery system inaccordance with a preferred embodiment of the present invention;

FIG. 6 is a schematic block diagram of a conventional broad beam lasersurgery system retrofitted in accordance with the teachings of thepresent invention; and

FIG. 7 is a schematic block diagram of a conventional scanning laserbeam surgery system retrofitted in accordance with the teachings of thepresent invention.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

The fail-safe systems disclosed are based on the control and monitoringof the energy in the laser beam exiting the optical rail and beamcontrolling optics of a laser surgery system. In preferred embodiments,the fail-safe system includes a laser energy monitor, analog-to-digitalconverter, and a programmed monitoring computer.

The monitoring system may be used, for example, in the two patientophthalmic surgical arrangement shown in FIG. 1. In such a case, twoidentical laser energy monitors may be installed at the ends of theright and the left laser beam delivery systems (surgical stations) afterthe end 45° turning mirror. As discussed in greater detail below, eachenergy monitor may consist of a glass fluorescence filter, convertinglaser radiation into fluorescence light, and a silicon photo diode forlight detection. To operate the diode and the signal amplifier in linearmodes, several neutral density filters are used. The amplified photodiode signal goes to the analog-to-digital converter (preferably acircuit card installed into the monitoring computer or an additionalcomputer).

Two independent computers may be used in the most preferred embodimentof the present invention. One computer is the treatment computer, thesecond computer is the monitoring or fail-safe computer. The treatmentcomputer drives the iris/slit/axis motors in the spatial modulator andgenerates the appropriate trigger pulses to the laser according to atreatment/calibration algorithm.

The monitoring computer measures, records, and monitors the energydetected by the energy detector for each pulse fired. The monitoringcomputer compares the energy values of the treatment algorithm to apredetermined calibration curve and simultaneously runs fail-safealgorithms. The treatment algorithm and the monitoring algorithm areequivalent. The monitoring computer receives the triggering signal sentto the laser by the treatment laser. Live and simultaneous monitoring ofthe entire treatment dose is performed by the system.

To avoid rather complicated calculations of iris, mask or spotgeometrical area and the influence of functional non-linearity of thephoto diodes and A/D converter or measurement accuracy, a calibrationcurve approach may be used. A calibration curve is generated at thebeginning of every surgery period. This is accomplished with an initialcalibration process. The calibration curve may be generated by running acalibration algorithm on the treatment laser and measuring and storingmeasured pulse energy values for each slit and iris setting from 6.0 mmdown to 1.0 mm with 0.5 mm increments. The fail-safe computer programgenerates a calibration curve based on the photo diode signal value ofan average of 20 consecutive laser pulses taken at each position of theiris and slit. When a treatment ablation algorithm is executed, themonitoring computer receives, after every laser pulse the digitizedphoto detector signal which is compared to a reference value obtainedfrom the calibration curve, the reference value indicating the expectedenergy value for the particular spatial dimensions of the pulse thenbeing administered.

The monitoring computer software compares the measured energy value witha reference value determined from the treatment parameters and treatmentalgorithm. Even though the system monitors laser pulse energy, itscomparison with reference values from the calibration curve for theproper iris/slit dimension is equivalent to monitoring the energy of theablating laser beam.

The monitoring computer may be programmed with values of acceptabledeviation between the monitored energy and reference energy values. Forexample, an acceptable deviation in treatment energy may include +/−10%deviation range from the calibration curve. If 10 consecutive laserpulses are outside of the above assigned ranges, the monitoring computerinitiates a continuous warning beep, and after 3 seconds will interruptthe laser triggering through a relay block unless the laser operatordoes so earlier.

Both the treatment and monitoring computers track and store all data ofa patient's treatment algorithm, energy etc. and if the treatment isinterrupted or stopped, the treatment data will be available to resumetreatment after the problem is resolved. Fail-safe features incorporatedinto the system include a maximal/minimal range of treatment energy,storage of treatment data, and an uninterruptable power supply system tomaintain both the treatment computer and the monitoring computer in theevent of a power failure.

Monitoring proper operation of the iris/slit mechanism is a function ofthe monitoring computer software, and is accomplished throughcomparisons of measured energy values by the photo diode with expectedenergy values for the specific treatment algorithm and the particulariris/slit dimensions called for by the algorithm. For example, thetreatment computer could signal the iris to be 4 mm. However, the irismay be “stuck” at 5 mm. The fail-safe system would monitor the pulse andindicate too high an energy value as compared with the reference valuefor the expected 4 mm iris. A value associated with the “stuck” 5 mmiris would be recorded.

Another feature of the laser dual computer fail-safe system requires theoperator to enter the patient treatment data twice, once into thetreatment computer and a second time into the monitoring or fail-safecomputer. This dual entry requirement provides for an opportunity todouble-check the current patient name, eye, and desired correction forrefractive error.

Details of the system of the present invention will now be describedwith reference to the drawings.

FIG. 3 is a cross-sectional side elevation of a portion of an arm of thesystem of FIG. 1 including a laser energy monitor 99 and a surgicalmicroscope mount 100. A laser beam from the optical rail and shuttlingdevice is shown at 101. The pulses making up the beam have already beenspatially modulated. The beam impinges on a beam-splitter 102. Inpreferred embodiments, the beam splitter is a fused silica coated glassplate with a principle plane oriented at a 45° angle with respect to thelaser beam 101. The front surface of the plate 102 may reflectapproximately 95% of the energy of the laser beam (reflected beam 103)to the target as indicated at 104. A low energy transmitted beam 106passes through the beam-splitter and impinges on a detector opticalsystem 108. In preferred embodiments the detector optical systemincludes a glass filter/diffuser 110 which diffuses the laser light.Advantageously, a fluorescent media 112 is located at the diffuser. Thefluorescent media may have the effect of changing the wavelength of theincident light. For example, diffused 193 nm laser radiation may beconverted into blue-green fluorescent light.

One or more neutral density filters 114 may be provided to reduce theintensity of the light received by the photo detector, such as photodiode 120. This intensity reduction is provided to permit the photodetector and associated analog amplifier 122 to operate in a generallylinear response mode across a range of expected incident light energies.

The amplifier 122 produces a signal 124. In preferred embodiments, thesignal is a voltage pulse which is selected by time-windowing circuitryin the monitoring computer. The windowing is triggered by the triggeringof the laser system to produce a treatment pulse. The peak height of thevoltage pulse is used as an indication of the energy of the treatmentpulse delivered to the patient, as will be discussed below.

FIG. 3(a) illustrates an alternative embodiment of FIG. 3 in whichsimilar features are identified by like numerals. In FIG. 3(a) opticalbaffles 126 and 128 have been located between the photo detector 120 andthe beam splitter 102. The optical baffles are arranged to absorbscattered light, including light not properly reflected from the frontsurface 130 of the beam splitter 102. Such scattered light may, forexample, be produced by organic or lens deposits or debris such asfluids spattered on the beam splitter during surgery. Such a deposit isdepicted at 132. Beams 134 and 136 represent light scattered by thedeposit at 132 and absorbed within the optical baffles 126 and 128. Thebaffle improves sensitivity of the measurement, for example, byexcluding light energy from measurement which has been scattered andthus is not indicative of energy delivered to the cornea of the patient.Fluorescence of organic materials may be also reduced or eliminated bygating the photo-detector.

FIG. 4 is a schematic block diagram illustrating aspects of the methodand system of the present invention. The system includes a laser 200,optical rail 202, photo detector 204, treatment computer 206 andfail-safe computer 208.

In operation, the system is initially calibrated by placing a laserlight energy detector at the location 210 and producing a series of testpulses having various spatial modulation under the control of thecalibration algorithm of the treatment computer. At the same time energyis monitored using photo detector 204 such as an energy monitor andfail-safe computer 208. The fail-safe computer develops a calibrationcurve or data using the calibration algorithm 211 and monitored energyvalues.

More specifically, in the calibration mode, an average of measuredenergy values from the A/D converter are associated with the variousspatial modulator settings. The result is a calibration curve or look-uptable which correlates various spatial modulator settings with anaverage voltage measurement from the energy monitor during thecalibration mode.

Treatment parameters are entered for a particular patient as indicatedat 212. The treatment parameter may include sphere correction, cylcorrection and cyl axis values. The data entry is made separately toboth the treatment computer 206 and the fail-safe computer 208. Thepatient 214 is readied for surgery.

The treatment computer 206 generates a treatment sequence of pulses andcontrols the spatial modulator 216 in accordance with commands derivedby a conventional treatment algorithm from the treatment parameters. Thelaser 200 is triggered by signals on control line 218. These triggersignals are simultaneously provided to the fail-safe computer 208.

Pulses produced by the laser 200 are spatially modulated and travelalong optical path 220. The beam splitter 222 reflects the pulses to thepatient's cornea and transmits a portion of the beam to the photodetector 204. Signals from the photo detector are applied to the A/Dconverter 224, which may be part of the circuitry hardware of thefail-safe computer 208.

Pulses from control line 218 and data entered as treatment parametersare processed by the treatment algorithm 226 resident in the fail-safecomputer 208. The monitoring computer calls up a value from thecalibration curve or look-up table which corresponds to the spatialmodulation of the pulse being administered. The result is a referencevalue related to the prescribed energy for the being pulse delivered tothe patient. This reference value is indicated at 227. The referencevalue is compared to a monitor energy value 229 derived from the signalfrom the photo detector 204. The comparison is indicated at 230.

Alarm limits may be input to the fail-safe computer 208. The alarmlimits are employed to generate a control or alarm signal which isoutput to the relay block 232. The relay block may trigger alarm 234 orcommand a shut down of the laser 200.

Calibration data, treatment parameters, energy monitor data, alarmlimits and comparison data may be stored in a memory 235 in fail-safecomputer 208.

The system described above has been tested in an ophthalmic surgeryexcimer laser system. The laser output at each surgical station was setat 38 mJ at 6 mm of iris opening by adjusting the high voltage settingof the excimer laser. The corresponding digital value of photo diodesignal was set as a reference energy value. Initial qualitative tests at6 mm iris/slit opening included blocking of about 12% of laser apertureat different points. In all cases, the fail-safe mechanism workedproperly reacting to the energy deficiency in the beam. Quantitativetests consisted of intentional decrease/increase of laser energy outputby adjusting the excimer laser voltage at different iris/slit positions.A JMAX 43/EM400 energy meter was used to measure the output laser energyat the treatment plane. The following table presents the test results:Iris/slit opening Initial (mm) energy, Shut Down Energy Iris Slit mJmJ + % MJ − % 1.5 open 2.6 2.9 11 2.3 11 6.0 2.0 14 15.5 11 12.5 11 3.0open 10.0 11.0 10 9.0 10 6.0 4.5 25 27.5 10 22.5 10 5.0 open 27 30.0 1124.4 10

Additional tests were conducted to simulate a variety of malfunctions ofthe iris/slit mechanism. This was accomplished by entering values in thetreatment algorithms that simulated both partil and complete “sticking”of both the iris and slit while operating the monitoring fail-safecomputer with the correct algorithms.

In all cases, the fail-safe system detected the errors by sounding analarm and recording energy values that were either too high or too lowwith respect to the expected value for the proper iris or slitdimensions.

The test results show that the fail-safe mechanism operated inaccordance with its design. The dual computer fail-safe method monitorsthe operation of the iris/slit mechanism, the quality of the optics,firing mechanism and ablation algorithm as well as the laser itselfduring the actual patient treatment. The results show that the fail-safemechanism operated in accordance with its design. Its implementation isexpected to provide higher safety level for patient laser refractivetreatments.

Optionally a second photo detector 250 may be employed to directlymonitor the output of the laser 200 at the beginning of the opticalrail. Advantageously, a beam splitter 252 directs a portion of the laserpulses produced by the laser 200 to the photo detector 250. Outputsignals from the photo detector are monitored by the fail safe computer208. The purpose of this additional detector is to provide normalizationof laser output fluctuations, thereby increasing the sensitivity of thefail safe system. This is important because lasers in conventionalcommercial systems fluctuate 10% or more from pulse to pulse and mayexhibit as much as a 50% drop in output over a single patient treatment.By incorporating this additional detector, the fail safe system shouldbe able to detect 2% or less in energy changes from pulse to pulse.Signals obtained by the photo detectors 250 and 204 may be used by thefail safe computer to differentiate performance anomalies caused by thelaser from those caused by components failures in the optical rail orforeign material on the optical surfaces of the system.

FIG. 5 is a schematic block diagram illustrating the use of an areaarray photo detector and histogram in a scanning spot laser surgerysystem in accordance with a preferred embodiment of the presentinvention. In FIG. 5, a laser 300 produces a beam 302 which is focusedto a relatively small spot size by beam focusing optics 304. The focusedbeam is scanned by beam scanning optics 305 in accordance with atreatment program in the conventional manner. A beam splitter 306transmits a portion of the scanned beam to the cornea 308 of thepatient. Another portion of the beam is reflected through the beamsplitter 306 to an electronic camera 310 such as one employing an areaphoto detector such as a CCD. Preferably, the second portion of the beamis directed to a luminescent screen 307 located at the same distancefrom the scanner as the plane of the patient's cornea. The screen 307converts the laser beam to visible light. An imaging lens 309 focuses animage of the beam or spot pattern for use by the electronic camera 310.A computing device 312 receives signals from the electronic camera andproduces signals representative in value of the spacial energydistribution of one or a series of laser pulses. This information may bestored in memory 314, for example, to enhance patient records and/or forlater evaluation the performance of the system or system drift. Thesignals may also be displayed, for example, on a display monitor 315.The display may take the form of a histogram such as that shown at 316.In the figure the blackened squares, Xs and dots represent pulsefrequency and/or integrated energy delivered to particularly areaincrements on the cornea of the patient over a selected time interval orover the full treatment period. Generally, the histogram of the exampleshows a spherical energy delivery profile with the highest energydelivered to the center 318 of the cornea. An anomaly, for example,caused by fluid spattered on the beam splitter is shown by the energydrop-off at 320. It will be understood that such a histogram provides aneffective indication of system malfunction.

FIG. 6 is a schematic block diagram illustrating the retrofitting of aconventional broad beam laser surgery system in accordance with theteachings of the present invention. The apparatus within the dotted linebox 400 represents a conventional broad beam laser surgery system suchas an “SVS Apex” system manufactured by Summit Technology, Inc. Thesystem includes a treatment computer 401 which controls a treatmentsequence of pulses delivered to the cornea of the patient and a highoutput energy, low to moderate repetition rate excimer laser 402. Atypical output of the laser is 200 to 300 mJ at 193 nm with a repetitionrate of 10 to 40 Hz. The laser may include an internal laser outputenergy detector 404 to monitor the output pulse energy. After exitingthe laser, the beam travels along optical path 406 to beam focusingoptics 408, beam homogenizer 410, and beam shaper (iris and slit) 412which operate under the control of the treatment computer 401. Imagingoptics 414 creates the image of the beam shaper diaphragm in thetreatment plane after the beam is turned toward the patient's cornea 415by the turning mirror 416. Some such systems have an output beamsplitter 418 and an energy monitor 420 for calibration purposes.

As shown in FIG. 6, the conventional broad beam laser surgery system 400can be modified to provide real-time monitoring of the output laserpulses taking into account the actual dimensions of the iris/slit duringtreatment. For example, should the beam shaper fail after calibration,the system of FIG. 6 as modified could detect such a failure and preventan incorrect ablation pattern being administered to the patent.

The retrofitting shown in FIG. 6 involves the addition of a fail safecomputer 422 having some or all of the features of the fail-safecomputer discussed above. The turning mirror 416 may be used as a beamsplitter to permit transmission of a portion of the energy of the pulsesbeing reflected by the turning mirror toward the patient. A photodetector system 424, such as of the type described in connection withFIG. 3(a) may be used to produce monitoring signals indicative of thelaser pulses delivered to the cornea of the patient. The monitoringsignals are transmitted from the photo detector system 424 to thefail-safe computer 422. The fail-safe computer may also receive amonitoring signal from the laser output energy detector 404. Finally,the fail-safe computer may send signals to and receive signals from thetreatment computer related, for example, to the triggering of the laserand the current settings of optical elements 408, 410 and 412.

In operation, the system is first calibrated as discussed above. Theevaluation of the laser pulses after they have passed through thecontrollable optical elements and normalization of these measurementsusing the signals from the laser output detector 404 will allow asignificant improvement in monitoring the performance of the system anddetection of the source of system malfunction, e.g., optical elementfailure, instability due to laser output fluctuations, etc. The use ofdigital electronics makes it possible to measure the energy of laserpulse striking the cornea with an accuracy of better than 1%. This isenough to track the difference between actual and programmed expansionof iris/slit mechanism within a few laser pulses. Further treatment canbe halted in a timely fashion to avoid incorrect patient corneaablation. This monitoring is made possible by the precise measurement ofthe energy of pulses directed at the patient and comparison of it withexpected energy. As discussed above, this energy value is derived from acalibration curve at the appropriate dimension of the iris/slitdiaphragm taken from each laser pulse in the predetermined treatmentsequence for ablating the cornea of the patient. Thus, malfunctioning ofthe system such as malfunction of the iris/slit expansion mechanism,changes of laser output energy, change or loss of nitrogen purge, orsudden deterioration of system optics can be tracked by the fail-safesystem and used to trigger system shut-off. Preferably, the fail-safecomputer may be connected to the laser as indicated by line 425 totransmit a shut-down command directly to the laser and by-pass thetreatment computer which itself may be the cause of the detected systemmalfunction.

To avoid a contamination of the output optics by accidental fluidsplashes during cornea flap preparation, a shield transparent to visiblelight such as glass or plastic plate 426 may be provided. The shield isselectively positioned “in” and “out” of the optical path by a specialdriver 428.

The plate 426 may be located in the optical path when no laser ablationis being performed. Advantageously, the plate is of good opticalquality, for example to permit observation of the cornea through theplate. The plate is moved out of the optical path during ablation,preferably on command from the treatment computer 401. Advantageously,the plate is disposable and is replaced periodically with a new plate toavoid build-up of contamination.

FIG. 7 is a schematic block diagram illustrating the retrofitting of aconventional scanning beam laser surgery system in accordance with theteachings of the present invention. The apparatus within the dotted linerectangular box 500 represents a conventional scanning beam laser systemsuch as a scanning beam laser surgery system using a 1 or 2 mm laserspot. The system includes a treatment computer 501 and a low pulseenergy, high-repetition rate excimer laser 502. A typical output of thelaser is 3 to 5 mJ at a repetition rate of 100 to 200 Hz. The opticalrail of the system may include an iris diaphragm 504; a focusing lens506 and an X-Y scanner 508 which acts as a turning mirror. The laser502, diaphragm 504 and X-Y scanner 508 operate under the control of thetreatment computer to provide laser pulses in accordance with atreatment sequence for the patient. The iris diaphragm 504 is set in thepath of the beam, which is transformed by a focusing lens 506 into asub-mm ablation spot to the cornea 507 of the patient after beingreflected by two turning mirrors of the X-Y scanner 508. There is eitheran internal pulse energy monitor 510 or an external one installed rightafter the scanning mirrors. This monitor may be used in a feedback loopto maintain a stability of laser output, or just an energy monitorlooped to the laser power supply to stop laser operation if the pulseenergy goes outside of the preset limits. A conventional, optional eyetracker 512 under system control may also be provided.

As shown in FIG. 7 the conventional scanning beam laser surgery system500 can be modified to provide real-time monitoring of the output energydistribution. The retrofitting involves the addition of a fail-safecomputer 514 which functions to compare separately entered treatmentprogram data with spatial energy distribution information obtained usingan imaging system (dotted line box 516). The fail-safe computer operatesin a manner similar to that described above.

In a preferred embodiment the imaging system 516 includes a beamsplitter 518 on the optical path to the cornea of the patient. A portionof the beam energy (e.g. 5%) is reflected by the beam splitter 518 tosemi-transparent, luminescent screen 520 located at the same distancefrom the scanner as the plane 521 of the patient's cornea. The screenconverts 193 nm UV radiation into visible light. An imaging lens 522focuses an image of the beam or spot pattern onto an electronic camera524 which includes an area array photo detector such as a CCD chip 526.

The major purpose of the fail-safe system of FIG. 7 is to monitor thescanning pattern rather than just the total energy of pulses deliveredto the patient.

Using the image obtained by the electronic camera 524 the fail-safecomputer tracks the position of the scanning spot for each laser pulseand compares it with the ablation algorithm pattern of the predeterminedtreatment sequence. In case of an X-Y scanner malfunction, for example,there will be an obvious discrepancy between programmed and actualpatterns. The fail-safe computer halts the operation of the system whena malfunction is detected, for example, by sending a shut-down commanddirectly to the laser over control line 527.

While the CCD imaging system of FIG. 7 has been described in connectionwith the retrofitting of a scanning spot laser surgery system, it willbe understood that such an imaging system may also be used inconjunction with a broad beam laser surgery system such as shown in FIG.6.

To further improve the reliability of the entire system, a shield 528and shield driver 530 may be provided similar in construction andfunction to the shield and driver discussed in connection with thesystem of FIG. 6. The shield and driver may operate under the control ofthe treatment computer 501.

While the present invention has been described with reference to certainpreferred embodiments, the scope of the invention to be protected isdetermined by the following claims and their appropriate range ofequivalents.

1. In a system for producing a predetermined treatment pattern of laserpulses for selectively ablating the cornea of a patient, said systemincluding a laser for producing laser light pulses, an electro-opticalsystem for controlling pulses of laser light from the laser so thatselected portions of the cornea of the patient are ablated in accordancewith the predetermined treatment pattern and a treatment computer whichruns a treatment algorithm based on inputted treatment parameters toproduce the predetermined treatment pattern, a monitoring system formonitoring the delivered laser pulses comprising: a detector forproducing signals during treatment indicative of sampled laser pulsesbeing delivered to the patient over a selected time interval; and afail-safe computer for separately running the treatment algorithm toprovide reference values for sampled pulses responsive to separatelyinputted treatment parameters, for comparing signals from the detectorwith the reference values; and for providing a signal indicative of theperformance of the system in response to the comparison.
 2. The systemof claim 1, further comprising means for producing a display of thespatial energy distribution of the laser pulses being delivered to thepatient.
 3. The system of claim 1 further comprising memory for storingenergy distribution information derived from the signals produced by thedetector.
 4. The system of claim 1, further comprising means forcontrolling the production of the treatment pattern of laser pulses inresponse to the signal indicative of the performance of the system. 5.The system of claim 4, wherein the controlling of the system in responseto the signal indicative of the performance of the system includesshutting down the system upon detection of an improper spatial energydistribution.
 6. The system of claim 1, wherein the system is a broadbeam system using pulses having a spot diameter of from ½ to 8 mm on thecornea of the patient.
 7. The system of claim 1, wherein theelectro-optical controlling system scans the laser pulses across an areaof the cornea to be ablated.
 8. The system of claim 7, wherein thesystem is a flying spot scanner.
 9. The system of claim 8, wherein thesystem uses laser spots having a diameter between 1 and 2 mm and a pulserate between 50 and 200 Hz.
 10. The system of claim 7, wherein thesystem is a slit scanning laser system.
 11. The system of claim 1wherein the detector is an electronic camera and wherein the laserpulses are focused to produce images of the laser pulse spots.
 12. Thesystem of claim 1, wherein the detector is an electro-optic detector forproducing electronic monitoring signals in response to 193 nm UV laserlight pulses.
 13. A method for monitoring a laser surgery system whichproduces a sequence of varying types of treatment pulses in accordancewith a treatment algorithm run by a treatment computer, comprising thesteps of: sampling laser pulses in a sequence of calibration pulses ofvarious types, so as to apply a predetermined portion of light energy ofthe pulses to a photo detector; providing output signals of the photodetector to a monitoring computer and associating the output signals ofthe photo detector with corresponding calibration pulses of varioustypes to obtain a reference value for each type of pulse; samplingtreatment laser pulses so as to apply a predetermined portion of thelight energy of each treatment pulse to the photo detector; andcomparing an output signal from the photo detector corresponding to atreatment laser pulse with a reference value for that type of pulse,wherein the reference value is obtained by using a treatment algorithmin the monitoring computer to identify the type of pulse which should bebeing administered in the treatment sequence and to select thecorresponding reference value for that type of pulse.
 14. The method ofclaim 13, wherein the treatment algorithm run in the treatment computeris the same treatment algorithm used by the monitoring computer.
 15. Themethod of claim 14, wherein treatment parameters are separately appliedto the treatment computer and monitoring computer for use in thetreatment algorithm.
 16. The method of claim 15, wherein the surgery isophthalmic laser surgery and the treatment parameters are refractive andastigmatism corrections appropriate for the patient.
 17. The method ofclaim 16, wherein the treatment parameters are used by the treatmentcomputer to select iris settings and slit dimensions which vary thespatial dimensions of the laser pulses to produce the various types oflaser pulses.
 18. A system for providing and monitoring laser pulsesproduced in accordance with a predetermined treatment sequence anddirected at the cornea of a patient to modify the cornea by photoablation and for verifying that the predetermined treatment sequence ofpulses is being delivered to the patient comprising: a laser forproducing laser pulses; an electro-optical system for controlling thepulses in response to signals from a first, treatment computer whichcontrols the electro-optical system in accordance with a treatmentalgorithm based on inputted treatment parameters; a detector fordetecting calibration pulses and pulses in the treatment sequence; and asecond, fail-safe computer for monitoring the performance of the systemwhile the treatment sequence is ongoing by comparing the treatmentmonitoring signals for at least some of the treatment pulses withcorresponding reference values derived from the calibration pulses, thereference values being indicative of the expected treatment monitoringsignals for treatment pulses produced during the treatment sequence,said reference values being determined from data entered into thefail-safe computing device separately from the data entered into thetreatment computing device, said separately entered data beingindicative of the patient's treatment sequence, and from at least onedetected calibration pulse for the same type of pulse measured duringcalibration.
 19. The system of claim 18 further comprising a beamsplitter which acts as a turning mirror and reflects laser pulses fromits front surface directly to the cornea of the patient.
 20. The systemof claim 19, wherein laser light received by the detector is transmittedthrough the beam splitter.
 21. The system of claim 19, wherein the beamsplitter has a front surface mirror which reflects laser pulses to thecornea of the patient.